Recharging power sources of implantable medical devices

ABSTRACT

In some examples, a medical device system includes a first implantable medical device. The first implantable medical device (IMD) may comprise circuitry configured to at least one of deliver a therapy to a patient or sense a physiological signal from the patient; generate stimulation deliverable to a patient; a first rechargeable power source; and a secondary coil coupled to the first rechargeable power source, the secondary coil configured to charge the first rechargeable power source via inductive coupling with a primary coil of an external charging device. The medical device system may comprise processing circuitry configured to control charging of the first rechargeable power source based on a charge state of a second rechargeable power source of a second IMD.

TECHNICAL FIELD

The disclosure relates to medical devices, and more particularly, tosystems and techniques for recharging power sources of one or moreimplantable medical devices.

BACKGROUND

Implantable medical devices may be used to monitor a patient conditionand/or deliver therapy to the patient. In long term or chronic uses,implantable medical devices may include a rechargeable power source(e.g., comprising one or more capacitors or batteries) that extends theoperational life of the medical device to weeks, months, or even yearsover a non-rechargeable device.

When the energy stored in the rechargeable power source has beendepleted, the patient may use an external charging device to rechargethe power source. Since the rechargeable power source is implanted inthe patient and the charging device is external of the patient, thischarging process may be referred to as transcutaneous charging. In someexamples, transcutaneous charging may be performed via inductivecoupling between a primary coil in the charging device and a secondarycoil in the implantable medical device. When a current is applied to theprimary coil and the primary coil is aligned to the secondary coil,electrical current is induced in the secondary coil within the patient.Therefore, the external charging device does not need to physicallyconnect with the rechargeable power source for charging to occur.

SUMMARY

This disclosure describes systems, devices, and techniques forrecharging power sources of one or more medical devices. When multipleimplantable medical devices receive power from an external chargingdevice, at least one of the medical devices and/or the external chargingdevice may manage at least one aspect of the charging process to addressdifferences in charge status between each medical device. In thismanner, a power source of a first medical device and a power source of asecond medical device can be recharged at the same time.

For example, an external charging device may transcutaneously transmitenergy to one or more rechargeable power sources of one or morerespective IMDs. The external charging device may query each IMD for apower source charge status and control one or more devices with a highercharge to consume more power prior to charging in order for the IMDs tostart charging with similar charge states of the respective powersources. In other examples, an IMD may directly receive communicationfrom another IMD regarding charge state and independently increase powerconsumption to equalize charge state of the power source to the otherIMD prior to charging. In other examples, an IMD may, by independentlydetecting a full charge state or in response to receiving instructionfrom an external charging device, stop charging the power source whilepower continues to be transferred by the external charge device. The IMDmay discontinue charging the power source by disconnecting the powersource from the secondary coil receiving the power or configuringcircuitry to prevent current from flowing in the secondary coil orassociated charging circuitry of the IMD.

In one example, this disclosure is directed to a medical systemincluding a first implantable medical device (IMD) comprisingstimulation circuitry configured to generate stimulation deliverable toa patient, a first rechargeable power source, and a secondary coilcoupled to the first rechargeable power source, the secondary coilconfigured to charge the first rechargeable power source via inductivecoupling with a primary coil of an external charging device, andprocessing circuitry configured to control charging of the firstrechargeable power source based on a charge state of a secondrechargeable power source of a second IMD.

In another example, this disclosure is directed to a method forcontrolling charging of a first rechargeable power source of a firstimplantable medical device (IMD) in a patient, the method includingreceiving, at a secondary coil of the first IMD, energy via inductivecoupling from a primary coil of an external charging device,controlling, by processing circuitry, charging of the first rechargeablepower source based on a charge state of a second rechargeable powersource of a second IMD.

In another example, this disclosure is directed to a medical systemincluding a first implantable medical device (IMD) that includesstimulation circuitry configured to generate stimulation deliverable toa patient, a first rechargeable power source; and a secondary coilcoupled to the first rechargeable power source, the secondary coilconfigured to charge the first rechargeable power source via inductivecoupling with a primary coil of an external charging device, a secondIMD that includes stimulation circuitry configured to generatestimulation deliverable to the patient, a second rechargeable powersource, and a secondary coil coupled to the second rechargeable powersource, the secondary coil configured to charge the second rechargeablepower source via inductive coupling with the primary coil of theexternal charging device, and processing circuitry configured todetermine a charge state of the first rechargeable power source and acharge state of the second rechargeable power source, control the firstIMD to achieve a target charge state of the first rechargeable powersource based on the charge state of the second rechargeable power sourceof the second IMD, and control delivering energy from the externalcharging device to the secondary coils coupled to the first and secondrechargeable power sources.

The details of one or more examples are set forth in the accompanyingdrawings and the description below. Other features, objects, andadvantages of examples according to this disclosure will be apparentfrom the description and drawings, and from the claims.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a conceptual diagram illustrating an example of a medicalsystem with multiple stimulation leads implanted in the brain of apatient.

FIG. 2 is a block diagram of the example of the implantable medicaldevice of FIG. 1.

FIG. 3 is a block diagram of the example of the external charging deviceof FIG. 1.

FIG. 4 is a flow diagram that illustrates an example technique forcontrolling charging of a power source of a medical device by anexternal charging device.

FIG. 5 is a flow diagram that illustrates an example technique forcontrolling charging of a power source of a medical device by anexternal charging device.

FIG. 6 is a flow diagram that illustrates an example technique forcontrolling charging of a power source of a medical device by anexternal charging device.

DETAILED DESCRIPTION

This disclosure describes systems (e.g., comprising one or more devices,components, sub-systems, or assemblies) and techniques (e.g., methods orprocesses) for recharging one or more power sources of one or morerespective medical devices. An external charging device is configured totransfer energy to an implantable medical device (IMD), and multiplemedical devices may receive this energy to charge respectiverechargeable power sources when the medical devices are implanted withinrange of the external charging device.

An IMD may include a rechargeable power source to extend the operationallife of the medical device. The IMD may receive power transcutaneouslyfrom an external charge device via a wireless charging scheme, such asinductive coupling. Typically, only a single IMD is positioned withinthe patient to receive the energy from the external charging device. Insome cases, two IMDs may be disposed within the patient, but each IMDmay be charged separately when the distance between the IMDs preventsone external charging device from delivering energy to both IMDs at thesame time. However, if two or more IMDs are positioned close enoughtogether, or otherwise close enough to the external charging device, themultiple IMDs will receive energy from the external charging device andpossibly charge the respective rechargeable power sources at the sametime. This scenario may cause a challenge during the charging process.For example, if a first rechargeable power source for a first IMD (e.g.,“IMD1”) reaches a full charge state prior to a second rechargeable powersource from a second IMD (e.g., “IMD2”), the first IMD may need todispose of the extra charging current as heat and possibly exposesurrounding tissue to an undesirable amount of heat. Any exampledescribed herein with respect to an “IMD” or “IMD1” may also apply toIMD2 or both of IMD1 and IMD2.

As described herein, one or more devices may operate to reducetemperatures of IMDs during charging and/or provide more efficientrecharging when multiple IMDs are inductively coupled to the sameexternal charging device. As discussed above, multiple medical devices(e.g., two IMDs, such as two neurostimulators) may be implanted ordisposed externally on a patient in proximity to one another such thatboth devices receive recharging energy from a common primary coil. Whenenergy is transferred via inductive coupling, for example, the secondarycoils would then be inductively coupled to the primary coil of theexternal charging device. In other words, the magnetic field of theprimary coil would induce current in both secondary coils of therespective IMDs. By using the techniques described herein, the externalcharging device, and the IMDs, may safely charge the respective powersources of multiple devices. For example, these techniques may reduceoverheating of the IMDs and thus undesirable heating of tissue aroundthe device. In an example, by using the techniques described herein,multiple power sources of multiple medical devices may be charged moreefficiently (e.g., faster) while increasing safety (e.g., better monitorof IMD or tissue temperature) for the patient. An example of thetechniques described herein includes controlling charging of a firstpower source of a first IMD while a second power source of a second IMDapproaches a target charge state (e.g., top-off, fully charged, oranother desirable or appropriate charge state), while still applyingfull power from the charging device and preventing overheating of tissueproximate to the first and second IMDs.

In an example, two IMDs may be close enough to each other such thatcharging energy from the charging device reaches both devices. In otherwords, recharging circuitry of both IMDs may receive charging energyfrom the charging device at the same time. In this case, a primary coilof the charging device may couple with two secondary coils of therespective two IMDs. In some instances, each IMD may receive a differentamount of the charging energy. Simultaneous charging of multiple IMDsmay decrease the amount of time needed to charge all IMDs of a patient,relative to charging each of the multiple IMDs individually andindependent of one another. The system may be configured to monitor howeach IMD is being charged to manage excess heat, for example. In someexamples, one or more of the IMDs may individually manage the chargingprocess to avoid excess charging or heating when multiple IMDs are beingcharged simultaneously. In other examples, one or more IMDs may receivecommunications from other IMDs regarding respective charge states ofpower sources and control charging of the power source based on thecharge states of the other IMDs. In other examples, the externalcharging device may receive information from the IMDs and controlcharging power and/or transmit instructions to one or more of the IMDsto take action that reduces charge state of one or more power sources,reduces charging rates of one or more power sources, and/or terminatescharging of the one or more power sources. In this manner, one or moredevices of the system may communicate to coordinate charging between allaffected IMDs.

In one example, a medical system includes processing circuitryconfigured to determine a charge state of a first rechargeable powersource of the first IMD (e.g., “IMD1”) and/or determine a charge stateof a second rechargeable power source of the second IMD (e.g., “IMD2”).IMD1 and IMD2 may be structurally identical or have differing componentsor different capabilities. IMD1 and IMD2 may be configured to providethe same therapy, different therapies, or even provide differentfunctionalities such as therapy delivery or monitoring services.Although described with respect to IMD1 and IMD2, the systems andtechniques may also apply to more than two devices (e.g., three or moremedical devices). IMD1 and IMD2 may communicate with each other viacommunication circuitry in some examples. The communication circuitrymay use wireless telemetry to transmit and/or receive information. Forexample, each IMD may be configured for two-way communication, or inother examples, different IMDs may be configured to only transmit oronly receive information. Each IMD in the system may communicate withone or more other devices, such as an external charging device or aprogrammer device. Any one device or combination of the devicesdescribed herein may implement the techniques described herein. In oneexample, IMD1 may include processing circuitry configured to controlcharging of one or more devices (e.g., including IMD1). In anotherexample, the external charging device may include processing circuitryconfigured to control charging of one or more devices.

In general, the processing circuitry may control charging of an IMDprior to or during a recharge session. In this manner, processingcircuitry within one or more of the IMDs in the patient, processingcircuitry of the external charger, or some combination thereof, maycontrol aspects of delivering charging power to the IMD such as when tocharge and at what power levels. Because the charge state of respectivepower sources for IMD1 and IMD2 may be imbalanced, for example, theprocessing circuitry may control one or both IMDs to balance therespective charge states prior to or during the recharge session.Balancing charge states of the IMDs may reduce the possibility that oneof the IMDs achieves a fully charged state prior to other IMDs. In thisdisclosure, a charge state of a power source may also be referred to asa charge state of an IMD since each IMD may include a respective powersource.

In one example, prior to the recharge session, if IMD1 has a highercharge state than IMD2, then processing circuitry within IMD1, IMD2,and/or the external charging device may control IMD1 to increase itspower consumption until the charge state of IMD1 is balanced (e.g., theequivalent, substantially equivalent, or within a tolerance ofequivalence) with IMD2. Once the charge states are balanced, theexternal charging device may start to deliver power to IMD1 and IMD2during a recharge session. In some examples, the external charger maywithhold charging during a recharge session until the charge states ofIMD1 and IMD2 are balanced and then start, or continue, charging duringthe recharge session until each IMD has reached a target charge state.In some examples, an IMD may increase its power consumption by turningon a power consuming feature, where the power consuming feature may notimpact therapy or monitoring functionality provided by the IMD. Examplesof power consuming features that may be initiated to consume powerinclude turning on wireless telemetry circuitry, executing one or moreprograms by processing circuitry of the IMD, and/or shunting energy fromthe power source and through a resistive load. IMD1 may increase itspower consumption, and thus reduce the charge state of the power source,in these or other ways. Commands to instruct IMD1 to consume additionalpower may be transmitted from processing circuitry within IMD1,processing circuitry from another IMD such as IMD2, or processingcircuitry within the external charging device. In some examples, controlof IMD1 may be shared or distributed between multiple devices.

A system with multiple IMDs receiving recharge power may control chargestate of the IMDs using other strategies in addition to, or alternativefrom, initial power consumption of the IMD with the higher charge state.For example, during a recharge session, if IMD1 will reach, or isexpected to reach, a target charge state (e.g., full charge) prior tothe target charge state of IMD2, then IMD1 may reduce the amount ofrecharge current that reaches its power source. In this way, the powersource of IMD1 may receive relatively less recharge energy (or none atall) while IMD2 continues to receive recharge energy from the sameexternal charging device. IMD 1 may reduce the amount of recharge energythat reaches the power source of IMD1 for a desired amount of time oruntil the charge states of the respective power sources of IMD1 and IMD2are balanced, such as described herein. In one example, IMD1 may reducethe amount of recharge current that reaches its power source by detuninga circuitry of the secondary coil of the IMD1 in which electricalcurrent is induced by the externa charging device. In some examples,detuning the circuitry (e.g., “opening a tuning switch”) of a coil isperformed as described in U.S. Pat. No. 9,042,995, incorporated hereinby reference in its entirety. In another example, IMD1 may disable aself-tuning oscillator of the IMD1 to reduce or prevent electricalcurrent from reaching the power source. In another example, IMD1 mayshunt recharge energy through a load (e.g., a resistive load) other thanthe first power source (e.g., other than the battery) to convert theundesired electrical current into heat instead of stored power in thepower source.

In the example of detuning the charging circuitry of the secondary coil,less energy may be transferred from the primary coil in the externalcharging device to the secondary coil of IMD1. However, this detuning ofthe charging circuitry may result in less electrical current and lowerheat generation as comparted to normal tuning of the charging circuitrythat is intended to generate higher electrical current for charging therechargeable power source. In one example, detuning the chargingcircuitry of IMD1 may include changing a resonant frequency of a tankcircuit, where the tank circuit includes the secondary coil of theIMD1's secondary coil. The charging circuitry may include the tankcircuit and other circuits such as rectification and/or filteringcircuitry. By detuning and changing the resonant frequency of the tankcircuit to be different than the frequency from the external primarycoil, lower current may be generated in the secondary coil than would beused for charging the rechargeable power source. In other examples, IMD1may include a self-tuning oscillator that is coupled across the tankcircuit. IMD1 may detune the tank circuit by disabling the self-tuningoscillator, such as switching the self-tuning oscillator out of the tankcircuit. In other examples, IMD1 may de-tune a rectifier circuit tode-tune the charging circuitry and reduce the amount of direct current(DC) generated in IMD1 from the alternating current (AC) power providedby the external charging device. For example, IMD1 may switch from fullwave rectification to half wave rectification to de-tune the rectifiercircuit.

In some examples, the charging device transmits a command that instructsIMD1 to open a circuit coupled to, or is a part of, the secondary coil.In other examples, IMD1 may proactively open a circuit coupled to, orpart of, the secondary coil. IMD1 may communicate with charging device20 to inform charging device 20 that IMD1 has opened the circuit thatprevents charging of the IMD1 power source. By creating an open circuitassociated with the secondary coil, the energy applied by the externalprimary coil may not induce a current in the secondary coil. Thetransmitted command may also instruct that an associated timer bestarted in response to opening the circuit. For example, the command mayinstruct IMD1 to open a circuit associated with the secondary coil andstart a countdown for IMD1 in which to keep the circuit open. In someexamples, the charging device may also track the countdown. Once thecountdown of the timer expires, IMD1 may close the circuit and re-enablecharging using the secondary coil or the charging device may againrequest IMD1 to open circuity associated with the secondary coil of IMD1if the charge state of IMD1 remains greater than the charge state ofIMD2. Processing circuitry of the medical system may be configured tocontrol one or more of these steps. In one example, a relay orsolid-state switch may be included in the 1 MB to control opening andclosing a circuit associated with the secondary coil.

In some examples, the systems and techniques described herein mayutilize thermal modeling or monitoring. For example, an IMD may includea temperature sensor that transmits data representative of a temperatureto processing circuitry, such as described further below. Processingcircuitry of the IMD thus may receive one or more temperature signalsfrom the temperature sensor or from multiple temperature sensors. Theprocessing circuitry may determine a thermal model of the 1 MB and/orsurrounding tissue based on the one or more temperature signals. Inother examples, the IMD or other device may generate a thermal dosage(e.g., energy delivered over a period of time) delivered to the patienttissue based on the temperature signals and/or known power output by theexternal charging device. These temperature signals may be generated byone or more temperature sensors of the IMD. In some examples, theprocessing circuitry may track the temperature of the device orsurrounding tissue over time based on the one or more temperaturesignals, thereby monitoring the thermal state of the IMD and/or tissuesurrounding the 1 MB. This thermal modeling or monitoring may enable theIMDs and/or external devices described herein to further reduce thepossibility of an implanted device delivering excess heat to a patient.The systems and techniques described herein may enable charging IMDswhen multiple IMDs receive power from a single external charging devicewhile avoiding excess charging of one of the IMDs (which may lead toexcess heat exposure for surrounding tissue). For example, the chargingdevice may transmit a relatively higher charging power, which may leadto faster charging rates of IMDs, because IMD1 may decouple from thecharging energy (e.g., due to a certain charge state or temperaturestate) while IMD2 remains coupled to continue charging. In this manner,an IMD may determine whether to reduce charge or continue charging basedon temperature information and the state of charge of the power sourcein the IMD. This ability to adjust how and/or when each 1 MB receivespower may reduce the need for the external charging device to lower thecharging power due to one of the IMDs reaching a full charge state priorto other IMDs receiving power from the same external charging device.

While the description of charging (also referred to as “recharging”) anIMD may refer to charging an implantable neurostimulator, the systemsand techniques described herein may be used with other types of medicaldevices or systems. For example, the devices, systems, and techniquesdescribed herein may be used with systems including medical devices thatdeliver electrical stimulation therapy to a patient's heart (e.g.,pacemakers, and pacemaker-cardioverter-defibrillators), drug pumps,monitoring devices, or other therapeutic, monitoring, or diagnosticdevices.

Although this disclosure generally describes the example of deep brainstimulation, the systems and techniques described herein may be used todeliver other types of electrical stimulation therapy (e.g., spinal cordstimulation, peripheral nerve stimulation, sacral nerve stimulation,pelvic nerve stimulation, gastric nerve stimulation, or vagal nervestimulation), stimulation of at least one muscle or muscle groups,stimulation of at least one organ such as gastric system stimulation,stimulation concomitant to gene therapy, and, in general, stimulation ofany tissue of a patient. In an example, the techniques described hereinmay be used with any system comprising multiple rechargeable powersources that could be charged from a single, or common, charging device.

FIG. 1 is a conceptual diagram illustrating an example of a medicalsystem 10 that includes multiple stimulation leads 15A and 15Bconfigured to be implanted in the brain 18 of a patient 12. In theexample of FIG. 1, medical system 10 includes a charging device 20configured to deliver energy to one or more implantable medical devices(IMDs) 14A and 14B such as via inductive coupling. For ease ofdescription, IMDs 14A and 14B may be collectively referred to as “IMDs14.” Similarly, for ease of describing two example IMDs, IMD 14A may bereferred to as “IMD1,” and IMD 14B may be referred to as “IMD2.” In anexample, IMDs 14 may be at least partially or fully implanted withinpatient 12. IMDs 14 may include or be coupled to a respective lead(e.g., lead 15A coupled to IMD 14A, and lead 15B coupled to IMD 14B).One or more electrodes of lead 15A and lead 15B are configured toprovide electrical signals (e.g., pulses or analog signals) tosurrounding anatomical regions of brain 18 in a therapy that mayalleviate a condition of patient 12. In some examples, one or both ofIMDs 14 may be coupled to more than one lead implanted within brain 18of patient 12 to stimulate multiple anatomical regions of the brain. Inan example, such as shown in FIG. 1, system 10 may include two IMDs 14that each include a lead. However, more than two IMDs may be disposed inpatient 12 in other examples.

Deep brain stimulation (DBS) delivered by one or both of IMDs 14 maytreat dysfunctional neuronal activity in the brain which manifests asdiseases or disorders such as Huntington's Disease, Parkinson's Disease,or movement disorders. Certain anatomical regions of brain 18 may beresponsible for producing the symptoms of such brain disorders. As oneexample, stimulating an anatomical region, such as the Substantia Nigra,in brain 18 may reduce the number and/or magnitude of tremorsexperienced by patient 12. Other anatomical regions that may receivestimulation therapy include the subthalamic nucleus, globus pallidusinterna, ventral intermediate, and zona inserta. Anatomical regions suchas these are targeted by the clinician during pre-operative planning andlead implantation. In other words, the clinician may attempt to positionthe leads 15A and 15B as close to these regions as possible for DBStherapy.

Typical DBS leads include one or more electrodes placed along thelongitudinal axis of the lead, such may be seen on leads 15A and 15B. Inone example, each electrode may be a ring electrode that resides alongthe entire circumference of the lead at one axial location on the lead.Therefore, electrical current from the ring electrodes propagates in alldirections from the active electrode. The resulting stimulation fieldreaches anatomical regions of brain 18 within a certain distance of thelead in all directions.

In other examples, lead 15A or 15B may have a complex electrode arraygeometry. A complex electrode array geometry include a plurality ofelectrodes positioned at different axial positions along thelongitudinal axis of the lead and a plurality of electrodes positionedat different angular positions around the circumference of the lead(which may be referred to as electrode segments). In some examples, thisdisclosure may be applicable to leads having all ring electrodes, or oneor more ring electrodes in combination with electrode segments atdifferent axial positions and angular positions around the circumferenceof the lead. In this manner, electrodes may be selected along thelongitudinal axis of leads 15A and 15B and along the circumference ofthe lead. A complex electrode array geometry may allow activating asubset of electrodes of leads 15A and 15B selected to producecustomizable stimulation fields that may be directed to a particularside of lead 15A or 15B in order to isolate the stimulation field aroundthe target anatomical region of brain 18.

IMDs 14 may be implanted on cranium 16, such as shown in FIG. 1. IMDs 14may be positioned elsewhere on cranium 16, such as closer together orfurther apart than shown in FIG. 1. The precise placement of IMDs 14 maybe determined to allow leads 15A and 15B to be implanted at desiredlocations within the respective hemisphere of brain 18. In an example,IMDs 14 may be positioned at least partially within respective holes orrecesses of cranium 16. In an example, IMDs 14 may be implantedelsewhere in the body of patient 12. For example, one or more IMDs 14may be implanted in the heart of patient 12, or within a thoracic spaceof patient 12. Regardless of the location of IMDs 14, leads 15A and 15Bmay be connected to respective IMDs 14A and 14B, and a distal end ofeach of leads 15A and 15B may be disposed through a burr hole in cranium16 and implanted within brain 18 to a predetermined location selected todeliver DBS or monitor brain activity.

Medical system 10 may also include multiple leads or electrodes on leadsof other shapes and sizes. In some DBS patients, two leads are implantedat symmetrical locations within brain 18 for bilateral stimulation tothe respective hemisphere. In particular, a first lead is placed in theright hemisphere of brain 18 and a second lead is placed at the mirroredlocation within the left hemisphere of the brain. Programmer 19 mayreceive input from a clinician that defines a desired stimulation fieldfor a first lead, and programmer 19 may generate a mirrored field forthe second lead, for example. The clinician may input find adjustmentsto programmer 19 to finely adjust either stimulation field toaccommodate the slight anatomical region differences between the leftand right hemispheres of brain 18.

While leads 15A and 15B are described for use in DBS applicationsthroughout this disclosure as an example, leads 15A and 15B, or otherleads, may be implanted at any other location within patient 12. Forexample, leads 15A or 15B may be implanted near the spinal cord,pudendal nerve, sacral nerve, or any other nervous or muscle tissue thatmay be stimulated, with IMDs also implanted away from cranium 16 inthese examples.

Medical system 10 may include external programmer 19, which may be ahandheld device, portable computer, or workstation that provides a userinterface to a clinician. The user interface may include a display topresent information to a user. In general, the user may interact withthe user interface. In an example, processing circuitry may provideinformation (e.g., a signal corresponding to a charge state of one ormore power sources) to the user interface. In some examples, the userinterface includes a keyboard, keypad, touch screen, mouse, or the like,for receiving input from the user. The user interface may include alight or speaker, such as may be used to provide an indication or alertto the user. For example, if the temperature sensor senses a temperatureof the IMD that meets a maximum limit, the processing circuitrydescribed herein may control the user interface, to initiate a blinkinglight or audible sound to alert the clinician to this or other relevantinformation.

The clinician may interact with the user interface to programstimulation parameters. The clinician may also interact with the userinterface to manually select and program certain electrodes of leads 15Aor 15B and adjust the resulting stimulation field with the anatomicalregions as guides, or defining one or more stimulation fields onlyaffect anatomical regions of interest. In an example, the clinician mayinteract with the user interface to determine a charge state of arechargeable power source of IMDs 14. For example, the charge state maybe represented as a percentage or numerical value, visually such as asymbol, or as an alert (e.g., a recharge indication).

Medical system 10 may provide the clinician with additional tools thatallow the clinician to program charging device 20, IMD 14A, or IMD 14B.FIG. 1 illustrates a communication link between charging device 20 andprogrammer 19. The communication link may represent a wired or wirelessconnection. In some examples, the communication link representstelemetry, as further described herein. Although not shown, any deviceof medical system 10 may be configured to communicate with any otherdevice of medical system 10. For example, external programmer 19 may beconfigured to communicate with IMD 14A, IMD 14B, and/or charging device20. In an example, charging device 20 may be configured to communicatewith IMD 14A, IMD 14B, and programmer 19.

In an example, the techniques described herein may be carried out by oneor more devices. In one example, the processing circuitry describedherein that controls charging of IMDs 14 may be within programmer 19 orwithin charging device 20. In another example, more than one device inmedical system 10 includes processing circuitry configured to carry outthe techniques described herein. In another example, IMD 14A includesprocessing circuitry configured to carry out the techniques describedherein. Since two or more devices of medical system 10 may communicate,medical system 10 may leverage multiple devices to perform a portion ofthe processing and control for charging IMDs 14.

Medical system 10 may include charging device 20 configured to deliverpower to each of IMDs 14 for recharging power sources within each IMD.In general, IMDs 14 may each include a power source (e.g., arechargeable power source). The power source may include a rechargeablebattery and/or capacitor. The power source may be coupled to a coil(e.g., a secondary coil), such as via charging circuity. The secondarycoil may inductively receive energy from a primary coil 48 (shown inFIG. 3) of charging device 20. Charging device 20 may deliver energy,such as inductively through the skin, or other tissue or anatomicalstructures, of patient 12 to recharge the power sources of IMDs 14.Charging device 20 may be used to recharge one or more rechargeablepower sources of IMDs 14 when implanted in patient 12. Charging device20 may be a hand-held device, a portable device, or a stationarycharging system. In any case, charging device 20 may include componentsnecessary to charge one or more rechargeable power sources throughtissue of patient 12. In other examples, charging device 20 include anexternal programmer (e.g., programmer 19) or other devices configured toperform additional functions. For example, when embodied as an externalprogrammer, charging device 20 may transmit programming commands to IMDs14 in addition to charge the rechargeable power sources. In anotherexample, charging device 20 may communicate with IMDs 14 to transmit orreceive information related to the charging of the rechargeable powersources. For example, IMDs 14A and 14B may transmit temperatureinformation or charge state information of the respective rechargeablepower sources. Other information may include information about, forexample, charge depletion rates during use, or any other informationrelated to power consumption and recharging of IMDs 14.

Charging device 20 and IMDs 14 may utilize any wireless power transfertechniques that are capable of recharging a rechargeable power source ofIMDs 14 when IMDs 14 are implanted within patient 14. In one example,medical system 10 may utilize inductive coupling between a coil ofcharging device 20 and respective coils of IMD 14A or 14B coupled to therespective rechargeable power source. In inductive coupling, chargingdevice 20 is placed near implanted IMD 14 such that a primary coil ofcharging device 20 is aligned with (e.g., placed over) a secondary coilof IMD 14A or 14B or both. Charging device 20 may then generate anelectrical current in the primary coil based on a selected power levelfor charging the rechargeable power source. An electrical current in theprimary coil creates a magnetic field that, when the primary andsecondary coils are aligned, induces an electrical current in thesecondary coil within one or both of IMDs 14. The primary coil maygenerate electromagnetic energy (e.g., radiofrequency (RF) energy) thatis received by the secondary coils depending on distance and alignmentto the primary coil. Since the secondary coils are associated with andelectrically coupled to the rechargeable power sources, the inducedelectrical current may be used to increase the loaded voltage, or chargelevel, of the rechargeable power sources. Although inductive coupling isgenerally described herein, any type of wireless energy transfer may beused to charge one or more rechargeable power sources.

As shown in FIG. 1, IMDs 14 may need to be placed on cranium 16 inlocations where each of leads 15 can reach the appropriate targetstimulation site within brain 18. However, this may result in IMDs 14being too close for charging device 20 to only charge one of IMDs 14 ata time. In other words, the electrical field generated by the primarycoil of charging device 20 to charge the power source of IMD 14A mayalso induce at least some electrical current in the secondary coil ofIMDs 14B. The benefit to this arrangement is that a single chargingdevice 20 may be used to charge both IMDs 14. However, simultaneouscharging of two separate IMDs can present difficulties with appropriatecharging rates for each IMD and ceasing energy delivery if one IMD isfully charged but the other IMD still requires more charging. AlthoughIMDs 14 may include mechanisms for diverting surplus electrical currentfrom a fully charged power source to a resistor or other device fordissipation as heat, generating heat in one IMD to remove excess currentmay result in undesirable temperatures for the patient when the otherIMD is also receiving charging energy.

As described herein, system 10 may employ one or more mechanisms forenabling recharge of multiple IMDs with a single charging device. Forexample, charging device 20 may control a higher power level IMD toreduce the remaining charge in order to create approximately equalcharge levels for both of IMDs 14. Therefore, each IMD 14 may be chargedfully and reach full charge at approximately the same time. In otherexamples, an IMD that reaches full charge first may detune or even opencircuit charging circuitry in order to reduce or stop the electricalcurrent generated in the secondary coil and delivered to therechargeable power source. In this manner, the IMD that still requiresadditional charging may continue to receive charging power withoutcausing excess heat to be generated by the IMD with the already fullycharged rechargeable power source.

FIG. 2 is a block diagram illustrating example components of an IMD 14.IMD 14 may correspond to IMD 14A, IMD 14B, or another medical device. Inthe example of FIG. 2, IMD 14 includes processing circuitry 22, powersource 24 (e.g., a rechargeable power source), charging circuitry 26,coil 28 (also may be referred to as secondary coil 28), temperaturesensor 30, memory 32, stimulation circuitry 34, communication circuitry36, and timer circuitry 38. In other examples, IMD 14 may include agreater or fewer number of components.

In general, IMD 14 may include any suitable arrangement of hardware,alone or in combination with software and/or firmware, to perform thevarious techniques described herein attributed to IMD 14 or processingcircuitry 22. In various examples, IMD 14 may include one or moreprocessors (e.g., processing circuitry 22), such as one or moremicroprocessors, digital signal processors (DSPs), application specificintegrated circuits (ASICs), field programmable gate arrays (FPGAs), orany other equivalent integrated or discrete logic circuitry, as well asany combinations of such components. IMD 14 also, in various examples,may include a memory 32, such as random access memory (RAM), read onlymemory (ROM), programmable read only memory (PROM), erasableprogrammable read only memory (EPROM), electronically erasableprogrammable read only memory (EEPROM), flash memory, comprisingexecutable instructions for causing the one or more processors (e.g.,processing circuitry) to perform the actions attributed to them.Moreover, although processing circuitry 22, stimulation circuitry 34,charging circuitry 26, and communication circuitry 36 are described asseparate, in some examples, processing circuitry 22, stimulationcircuitry 34, charging circuitry 26, and communication circuitry 36 arephysically and/or functionally integrated. In some examples, processingcircuitry 22, stimulation circuitry 34, charging circuitry 26, andcommunication circuitry 36 correspond to individual hardware units, suchas ASICs, DSPs, FPGAs, or other hardware units.

Memory 32 may be configured to store therapy programs or otherinstructions that specify therapy parameter values for the therapydeliverable by stimulation circuitry 34 and IMD 14. In some examples,memory 32 may also store temperature data from temperature sensor 30,temperature thresholds, instructions for recharging power source 24,circuit models, open-circuit voltage models, tissue models, thresholds,instructions for communication between IMD 14 and programmer 19 orcharging device 20, or any other instructions required to perform tasksattributed to IMD 14. In this manner, memory 32 may be configured tostore charge states of one or more rechargeable power sources.Processing circuitry 22 may be configured to determine an IMD (e.g., IMD14) that has a higher or lower charge state than another IMD bycomparing two charge states. In response to the comparison, processingcircuitry 22 may control charging circuitry 26, for example, of thehigher-charged IMD to open a circuit in charging circuitry 26 untilprocessing circuitry 22 determines that both IMDs have similar chargestates or are within an appropriate threshold of each other.

Generally, stimulation circuitry 34 may be configured to generate anddeliver electrical stimulation under the control of processing circuitry22. In some examples, processing circuitry 22 controls stimulationcircuitry 34 by accessing memory 32 to selectively access and load atleast one of the stimulation programs to stimulation circuitry 34. Forexample, in operation, processing circuitry 22 may access memory 32 toload one of the stimulation programs to stimulation circuitry 34. Insuch examples, relevant stimulation parameters may include a voltageamplitude, a current amplitude, a pulse rate, a pulse width, a dutycycle, or the combination of electrodes 17A, 17B, 17C, and 17D (or feweror greater electrodes) that stimulation circuitry 34 uses to deliver theelectrical stimulation signal. Although stimulation circuitry 34 may beconfigured to generate and deliver electrical stimulation therapy viaone or more of electrodes 17A, 17B, 17C, and 17D of a lead (e.g., lead15A or 15B), stimulation circuitry 34 may be configured to providedifferent therapy to patient 12. For example, stimulation circuitry 34may be configured to deliver drug delivery therapy via a catheter. Theseand other therapies may be provided by IMD 14. In this manner,stimulation circuitry 34 may be an example of a therapy moduleconfigured to generate and/or deliver a therapy such as electricalstimulation or drug therapy. The therapy module may include a drug pumpin the example IMD 14 delivering a drug to patient 12. In some examples,stimulation circuitry 34 may also be configured to sense physiologicalsignals (e.g., electrical signals from the brain such as anelectroencephalogram (EEG) or an electrocorticogram (ECoG), electricalsignals from other tissues, pressure, temperature, tissue chemistry, andthe like) from the brain or any other tissue of patient 12. In someexamples, IMD 14 may include sensing circuitry, in addition tostimulation circuitry 34, configured to sense one or more physiologicalsignals from patient 12 and generate an electrical signal representativeof the one or more physiological signals.

IMD 14 also includes components configured to receive power fromcharging device 20 to recharge power source 24, such as when powersource 24 has been at least partially depleted. As shown in FIG. 2, IMD14 includes secondary coil 28 and charging circuitry 26 coupled to powersource 24. Charging circuitry 26 may be configured to charge powersource 24 with power received from external charging device 20. Thepower generated by external charging device 20 is, in some examples,generated according to a selected power level determined by eitherprocessing circuitry 22 or charging device 20. Although processingcircuitry 22 may provide some commands to charging circuitry 26 in someexamples, processing circuitry 22 may not need to control any aspect ofrecharging in other examples.

Secondary coil 28 may include a coil of wire or other device in which anelectrical current can be induced via inductive coupling with a primarycoil disposed external to patient 12. Although secondary coil 28 isillustrated as a simple loop in FIG. 2, secondary coil 28 may includemultiple turns of wire. Secondary coil 28 may include a winding of wireconfigured such that an electrical current can be induced withinsecondary coil 28 from a magnetic field generated by the externalprimary coil. The induced electrical current may then be used by IMD 14to recharge power source 24. In this manner, an electrical current maybe induced in secondary coil 28 associated with power source 24. Theinduction of electrical current may be caused by a magnetic fieldgenerated by electrical current generated in the primary coil ofcharging device 20 and based on the selected power level. The couplingbetween secondary coil 28 and the primary coil of charging device 20 maybe dependent upon the alignment of the two coils. Generally, thecoupling efficiency increases when the two coils share a common axis andare in close proximity to each other.

Although inductive coupling is generally described as the method forrecharging power source 24, other wireless energy transfer techniquesmay additionally or alternatively be used. Any of these techniques maygenerate heat in IMD 14 that may be monitored, for example, bytemperature sensor 30.

Charging circuitry 26 may include one or more circuits that filterand/or transform the electrical signal induced in secondary coil to anelectrical signal capable of recharging power source 24. For example, inalternating current induction, charging circuitry 26 may include ahalf-wave rectifier circuit and/or a full-wave rectifier circuitconfigured to convert alternating current from the induction to a directcurrent for power source 24. The full-wave rectifier circuit may be moreefficient at converting the induced energy for power source 24. However,a half-wave rectifier circuit may be used to store energy in powersource 24 at a slower rate. In some examples, charging circuitry 26 mayinclude both a full-wave rectifier circuit and a half-wave rectifiercircuit such that charging circuitry 26 may switch between each circuitto control the charging rate of power source 24 and temperature of IMD14. As discussed above, charging circuitry 26 may be du-tuned bychanging the rectifier circuitry from full-wave to half-waverectification to reduce the amount of DC power sent to power source 24.

In some examples, charging circuitry 26 may include a tank circuit,which may include secondary coil 28. The tank circuit may be tuned tothe external primary coil in order to generate electrical current thatcharges power source 24. However, in some cases, IMD 14 may includecircuitry that is configured to change the resonant frequency of thetank circuit, or tune the tank circuit, as desired. The resonantfrequency of the tank circuit may be changed by variable reactanceprovided by a variable capacitance. For example, IMD 14 may include atuning switch that receives a control signal from processing circuitry22 to alter the state and ultimately vary the reactance of the tankcircuit that includes secondary coil 28. The tuning switch may open andclose to remove or add a capacitor in parallel with a hardwiredcapacitor, where the hardwired capacitor is in series with secondarycoil 28. In this manner the tuning switch may tune the tank circuit forrecharge or tune the tank circuit to a resonant frequency other than therecharge frequency to provide power management by reducing the receivedpower during recharge (e.g., detune the tank circuit). Other types ofcircuitry may also be used by charging circuitry 26 in order to detunecoil 28 and change the electrical current generated by coil 28 from thepower output by the external primary coil.

In other examples, IMD1 may include a self-tuning oscillator that iscoupled across the tank circuit. For example, an oscillator, such as asinusoidal power amplifier, may be coupled to the tank circuit to drivethe tank circuit at a target frequency for inductive coupling withprimary coil 48 of charging device 20. Processing circuitry 22 maydetune the tank circuit by disabling the self-tuning oscillator, such asswitching the self-tuning oscillator out of the tank circuit when lesscharge current is desired to be induced by secondary coil 28. In someexamples, disabling the self-tuning oscillator may not reduce powergenerating in IMD 1 as much as adding or removing capacitors asdiscussed above.

In some examples, charging circuitry 26 may include a measurementcircuit (e.g., a coulomb counter) configured to measure the currentand/or voltage induced in IMD 14 during inductive coupling. Thismeasurement may be used to measure or calculate the power transmitted topower source 24 of IMD 14 from charging device 20. In some examples,charging circuitry 26 or other circuitry may include an electrometer,coulometer or coulomb counter, which may measure the charge currentbeing applied to power source 24 and communicate this charge current toprocessing circuitry 22. In some examples, processing circuitry 22 maycontrol charging circuitry 26 to open a circuit of charging circuitry 26to prevent electrical induction and/or detune coil 28 of IMD 14 togenerate less power from charging device 20.

Power source 24 may include one or more capacitors, batteries, and/orother energy storage devices. Power source 24 may then deliver operatingpower to the components of IMD 14. In some examples, power source 24 mayinclude a power generation circuit to produce the operating power. Powersource 24 may be configured to operate through hundreds or thousands ofdischarge and recharge cycles. Power source 24 may also be configured toprovide operational power to IMD 14 during the recharge process. In someexamples, power source 24 may be constructed with materials to reducethe amount of heat generated during charging. In other examples, IMD 14may be constructed of materials that may help dissipate generated heatat power source 24, charging circuitry 26, and/or secondary coil 28 overa larger surface area of the housing of IMD 14.

Although power source 24, charging circuitry 26, and secondary coil 28are shown as contained within the housing of IMD 14, at least one ofthese components may be disposed outside of the housing. For example,secondary coil 28 may be disposed outside of the housing of IMD 14 tofacilitate better coupling between secondary coil 28 and the primarycoil of charging device 20. These different configurations of IMD 14components may allow IMD 14 to be implanted in different anatomicalspaces or facilitate better inductive coupling alignment between theprimary and secondary coils.

IMD 14 may also include temperature sensor 30. Temperature sensor 30 mayinclude one or more temperature sensors (e.g., thermocouples orthermistors) configured to measure the temperature of 1 MB 14.Temperature sensor 30 may be disposed internal of the housing of 1 MB14, contacting the housing, formed as a part of the housing, or disposedexternal of the housing. Temperature sensor 30 positioned within the IMDand may sense an internal temperature of the 1 MB. In an example,temperature sensor 30 may sense a temperature of the housing of the IMD.In other examples, temperature sensor 30 may be positioned on thehousing of the IMD and it may sense the temperature of the tissuesurrounding the 1 MB. Multiple temperature sensors may be positioned onor within the IMD in some examples.

As described herein, temperature sensor 30 may be used to directlymeasure the temperature of IMD 14 and/or tissue surrounding and/orcontacting the housing of IMD 14. Processing circuitry 22, or chargingdevice 20, may use this temperature measurement as tissue temperature todetermine a temperature model of IMD 14 or of the tissue surrounding 1MB 14. Although a single temperature sensor may be adequate, multipletemperature sensors may provide a better temperature gradient or averagetemperature of IMD 14. The various temperatures of IMD 14 may also bemodeled. Although processing circuitry 22 may continually measuretemperature using temperature sensor 30, processing circuitry 22 mayconserve energy by only measuring temperature during recharge sessions.Further, temperature may be sampled at a rate to determine adequatetemperature measurements or models, but the sampling rate may be reducedto conserve power as appropriate.

Processing circuitry 22 may also control the exchange of informationwith charging device 20 and/or an external programmer usingcommunication circuitry 36. Communication circuitry 36 may be configuredfor wireless communication using radio frequency protocols or inductivecommunication protocols. Communication circuitry 36 may include one ormore antennas configured to communicate with charging device 20, forexample. Processing circuitry 22 may transmit operational informationand receive therapy programs or therapy parameter adjustments viacommunication circuitry 36. Also, in some examples, IMD 14 maycommunicate with other implanted devices, such as stimulators, controldevices, or sensors, via communication circuitry 36. In addition,communication circuitry 36 may be configured to transmit the measuredtissue temperatures from temperature sensor 30, the charge state ofpower source 24 (e.g., a respective charge state from each of the powersources associated with IMDs 14A and 14B), for example. Communicationcircuitry of each of IMDs 14A and 14B may communicate information (e.g.,power source charge state information) to each other and to otherdevices, such as programmer 19, charging device 20, or others. In someexamples, tissue temperature may be measured adjacent to power source24.

In other examples, processing circuitry 22 may transmit additionalinformation to charging device 20 related to the operation of powersource 24. For example, processing circuitry 22 may use communicationcircuitry 36 to transmit indications that power source 24 is completelycharged, power source 24 is fully discharged, how much charge (e.g., thecharge current) is being applied to power source 24, the charge capacityof power source 24, the state-of-charge (SOC) of power source 24, or anyother charge information of power source 24. Processing circuitry 22 mayalso transmit information to charging device 20 that indicates anyproblems or errors with power source 24 that may prevent power source 24from providing operational power to the components of IMD 14.

Processing circuity 22 may determine the charge state of power source24. For example, processing circuitry 22 may include a voltage testercircuit coupled to power source 24 to determine the charge state (e.g.,voltage level) of power source 24. In some examples, processingcircuitry 22 determines the charge state as a voltage measurement value,as a percentage of full capacity, in relation to another power sourcecharge state (e.g., higher, same, similar, lower), or any combinationthereof. In some examples, a user interface (e.g., user interface 54 ofFIG. 3) indicates the charge state of one or more power sources. Forexample, the user interface may display a bar chart, graph, value, alight, or any other indication of charge state of the power source.

In an example, processing circuitry 22 may control timer circuitry 38 tobegin a countdown, such as during a recharge session. In an example,processing circuitry 22 may control one or more devices to perform aparticular task with a particular duration, such as may be timed viatimer circuitry 38. For example, processing circuitry 22 may controlcharging circuitry 26 to open a circuit for a desired amount of time(e.g., on the scale of seconds, minutes, or hours). Once the countdownexpires, processing circuitry 22 may control charging circuitry 26 toclose the circuit, such as to tune the IMD to the charging device (e.g.,change from a detuned state of the IMD).

FIG. 3 is a block diagram of an example of external charging device 20.While charging device 20 may generally be described as a hand-helddevice, charging device 20 may be a larger portable device or a morestationary device. In addition, in other examples, charging device 20may be included as part of an external programmer (e.g., programmer 19shown in FIG. 1) or include functionality of an external programmer. Inaddition, charging device 20 may be configured to communicate with anexternal programmer. As illustrated in FIG. 3, charging device 20 mayinclude primary coil 48, processing circuitry 50, memory 52, userinterface 54, communication circuitry 56, charging circuitry 58, andpower source 60. Memory 52 may store instructions that, when executed byprocessing circuitry 50, cause processing circuitry 50 and externalcharging device 20 to provide the functionality ascribed to externalcharging device 20 throughout this disclosure.

In general, charging device 20 includes any suitable arrangement ofhardware, alone or in combination with software and/or firmware, toperform the techniques attributed to charging device 20, and processingcircuitry 50, user interface 54, communication circuitry 56, andcharging circuitry 58 of charging device 20. In various examples,charging device 20 may include one or more processors (e.g., processingcircuitry 50), such as one or more microprocessors, DSPs, ASICs, FPGAs,or any other equivalent integrated or discrete logic circuitry, as wellas any combinations of such components. Charging device 20 also, invarious examples, may include a memory 52, such as RAM, ROM, PROM,EPROM, EEPROM, flash memory, a hard disk, a CD-ROM, comprisingexecutable instructions for causing the one or more processors toperform the actions attributed to them. Moreover, although processingcircuitry 50 and communication circuitry 56 are described as separate,in some examples, processing circuitry 50 and communication circuitry 56are functionally integrated. In some examples, processing circuitry 50and communication circuitry 56 and charging circuitry 58 correspond toindividual hardware units, such as ASICs, DSPs, FPGAs, or other hardwareunits.

Memory 52 may store instructions that, when executed by processingcircuitry 50, cause processing circuitry 50 and charging device 20 toprovide the functionality ascribed to charging device 20 throughout thisdisclosure. For example, memory 52 may include instructions that causeprocessing circuitry 50 to control charging circuitry 58, communicatewith IMD 14, or instructions for any other functionality. In addition,memory 52 may include a record of selected power levels, calculatedestimated energy transfers, or any other data related to chargingrechargeable power source 24. Processing circuitry 50 may, whenrequested, transmit any of this stored data in memory 52 to anothercomputing device for review or further processing.

In some examples, memory 52 may be configured to store measured chargestates of one or more power sources of one or more IMDs over time, ageof a power source 24, and/or any other factors that may affect voltageof a power source 24. In some examples, memory 52 may be configured tostore data representative of an energy absorption tissue model used byprocessing circuitry 50 to determine the energy absorption of tissue ata particular operating frequency. In some examples, memory 52 may beconfigured to store data representative of a tissue model used byprocessing circuitry 50 to calculate tissue temperature based on tissuemodel and power transmitted to rechargeable power source 24 over aperiod of time. Tissue model may indicate how temperate of tissuesurrounding IMD 14 changes over time.

User interface 54 may include a button or keypad, lights, a speaker thatgenerates audible sounds, a microphone that detects voice commands, adisplay, such as a liquid crystal (LCD), light-emitting diode (LED), orcathode ray tube (CRT). In some examples the display may be a touchscreen. As discussed in this disclosure, processing circuitry 50 maypresent and receive information relating to the charging of rechargeablepower source 24 via user interface 54. For example, user interface 54may indicate when charging is occurring, quality of the alignmentbetween secondary coil 28 and primary coil 48, the selected power level,current charge level of rechargeable power source 24, duration of thecurrent recharge session, anticipated remaining time of the chargingsession, or any other information. Processing circuitry 50 may receivesome of the information displayed on user interface 54 from IMD 14 insome examples.

User interface 54 may also receive user input via user interface 54. Theinput may be, for example, in the form of pressing a button on a keypador selecting an icon from a touch screen. The input may request startingor stopping a recharge session, a desired level of charging, or one ormore statistics related to charging rechargeable power source 24 (e.g.,the estimated energy transfer). In this manner, user interface 54 mayallow the user to view information related to the charging ofrechargeable power source 24 and/or receive charging commands.

Charging device 20 also includes components to transmit power torecharge rechargeable power source 24 associated with IMD 14. As shownin FIG. 3, charging device 20 includes primary coil 48 and chargingcircuitry 58 coupled to power source 60. Charging circuitry 58 may beconfigured to generate an electrical current in primary coil 48 fromvoltage stored in power source 60. Although primary coil 48 isillustrated as a simple loop in the example of FIG. 3, primary coil 48may include multiple turns of wire. Charging circuitry 58 may generatethe electrical current according to a power level selected by processingcircuitry 50 based on the estimated energy transfer. As describedherein, processing circuitry 50 may select a high power level, low powerlevel, or a variety of different power levels (e.g., three or moredifferent power levels) to control the rate of recharge in rechargeablepower source 24. In some examples, the power level may be selected basedon the determined temperature of one or more of IMDs 14. In someexamples, processing circuitry 50 may control charging circuitry 58based on a power level selected by processing circuitry 22 of at leastone of IMDs 14.

Primary coil 48 may include a coil of wire, e.g., having multiple turns,or other device capable of inductive coupling with a secondary coil 28disposed within patient 12. Primary coil 48 may include a winding ofwire configured such that an electrical current generated within primarycoil 48 can produce a magnetic field configured to induce an electricalcurrent within secondary coil 28. Primary coil 48 may be constructed ofcertain dimensions and/or driven to produce electromagnetic energy of aparticular frequency selected for secondary coil 28. The inducedelectrical current may then be used to recharge rechargeable powersource 24. In this manner, the electrical current may be induced insecondary coil 28 associated with rechargeable power source 24. Thecoupling efficiency between secondary coil 28 and primary coil 48 ofcharging device 20 may be dependent upon the alignment of the two coils.Generally, the coupling efficiency increases when the two coils share acommon axis and are in close proximity to each other. Therefore, if twosecondary coils of respective IMDs 14 receive power from a singleprimary coil 48, one IMD may receive more power than the other IMD.Primary coil 48 may be configured to couple with multiple secondarycoils at once. For example, primary coil 48 may be constructed ofdimensions to couple with multiple secondary coils of respectivemultiple IMDs to recharge power sources of the IMDs. User interface 54of charging device 20 may provide one or more audible tones or visualindications of the alignment.

Charging circuitry 58 may include one or more circuits that generate anelectrical signal, and an electrical current, within primary coil 48.Charging circuitry 58 may generate an alternating current of specifiedamplitude and frequency in some examples. In other examples, chargingcircuitry 58 may generate a direct current. In any case, chargingcircuitry 58 may be configured to generate electrical signals that, inturn, causes primary coil 48 to generate a magnetic field that transmitsvarious levels of power to IMD 14. In this manner, charging circuitry 58may be configured to charge rechargeable power source 24 of IMD 14 withany desirable power level.

A power level may specify a wattage, electrical current in primary coil48 or secondary coil 28, current amplitude, voltage amplitude, or anyother parameter that may be used to modulate the power transmitted fromcoil 48. The parameters of the power level may be selected based onhardware characteristics of charging device 20 and/or IMD 14.

Power source 60 may deliver operating power to the components ofcharging device 20. Power source 60 may also deliver the operating powerto drive primary coil 48 during the charging process. Power source 60may include a battery and a power generation circuit to produce theoperating power. In some examples, the battery may be rechargeable toallow extended portable operation. In other examples, power source 60may draw power from a wired voltage source such as a consumer orcommercial power outlet.

Although power source 60 and charging circuitry 58 are shown within ahousing of charging device 20, and primary coil 48 is shown external tocharging device 20, different configurations may also be used. Forexample, primary coil 48 may also be disposed within the housing ofcharging device 20. In another example, power source 60, chargingcircuitry 58, and primary coil 48 may be all located external to thehousing of charging device 20 and coupled to charging device 20.

Communication circuitry 56 supports wireless communication between IMD14, charging device 20, and/or programmer 19 under the control ofprocessing circuitry 50. Communication circuitry 56 may also beconfigured to communicate with another computing device via wirelesscommunication techniques, or direct communication through a wiredconnection. In some examples, communication circuitry 56 may besubstantially similar to communication circuitry 36 of IMD 14 describedherein, providing wireless communication via an RF or proximal inductivemedium. In some examples, communication circuitry 56 may include anantenna, which may take on a variety of forms, such as an internal orexternal antenna. In some examples, communication to IMD 14 may takeplace via modulation of power from primary coil 48 that is detectable byIMD 14.

Examples of local wireless communication techniques that may be employedto facilitate communication between charging device 20 and IMD 14include RF communication according to the 802.11 or Bluetoothspecification sets or other standard or proprietary telemetry protocols.In this manner, other external devices may be capable of communicatingwith charging device 20 without needing to establish a secure wirelessconnection.

FIG. 4 is a flow diagram that illustrates an example of a technique forcontrolling charging of a power source (e.g., power source 24) of amedical device by an external charging device. Processing circuitry 50of charging device 20 is described as generally performing the techniqueof example FIG. 4. However, in other examples, the technique of FIG. 4may be performed by processing circuitry 22 of IMD 14, processingcircuitry of another IMD, processing circuitry of external programmer19, or by any processing circuitry of any single device described hereinor any combination thereof. In other words, some functionality may beperformed by distributed computing processes. In some examples, one orboth of programmer 19 and charging device 20 receive information fromIMDs 14. Processing circuitry 50, for example, may control IMD 14A andIMD 14B prior to and during charging. For example, processing circuity50 may control IMD 14A to shunt energy through a resistive load prior toa recharging session.

As shown in the example of FIG. 4, processing circuitry 50 of chargingdevice 20 may receive data from first and second IMDs (e.g., IMD1 andIMD2 or IMD 14A and IMD 14B) that is indicative of respective chargestates (102). In some examples, communication circuitry 36 of therespective IMD transmits the data indicative of the charge state of eachpower source 24 to charging device 20. Processing circuitry 50 may thendetermine the charge state of the first power source of IMD1 and thecharge state of the second power source of IMD2 based on informationsuch as the received data (104).

Processing circuitry may control IMD1 to achieve a target charge statebased on the charge state of IMD2 (106). In an example, if IMD2 has acharge state less than the charge state of IMD1, then the processingcircuitry may control circuitry of IMD1 (e.g., processing circuitry 22or charging circuitry 26 of IMD1) to achieve the target charge state,such as a charge state similar to the charge state of IMD2. In someexamples, the target charge state of IMD1 is within a threshold of thecharge state of IMD2 (e.g., within about 5% to about 10% of the chargestate of IMD2 or within a threshold voltage value of IMD2). Processingcircuitry 50 may transmit a command to IMD1 to perform some action thatwill achieve the target charge state (e.g., reduce the charge state ofpower source 24 of IMD1. For example, processing circuitry 50 maytransmit a command for IMD1 to turn on a power consuming feature ofIMD1, such as powering a communication antenna, powering a sensor, orprocessing circuitry 22 performing calculations. Typically, these powerconsuming features are selected so as to not impact therapy delivery orother therapeutic or sensing functions. In some examples, processingcircuitry 50 may initiate a telemetry session, run a program on amicro-processor (such as processing circuitry 50), shunt energy througha resistive load, or another task. If processing circuitry 50 determinesthat IMD1 has not reached the target charge state (“NO” branch of block107), then processing circuitry 50 continues to control IMD1 to achievethe target charge state (106). If processing circuitry 50 determinesthat IMD1 has reached the target charge state (“YES” branch of block107), then charging device 20 may deliver energy to the first and secondIMDs (108). In general, before, during, or after the preceding steps,charging device 20 may deliver energy to the first and second IMDs(108).

Charging device 20 may perform the technique of FIG. 5 as part of anyrecharging of IMDs implanted in patient 12. Alternatively, externalprogrammer 19 may interface between charging device 20 and IMDs 14 inorder to relay data and/or commands for one or more of IMDs 14 to senddata related to the current charge state of the respective power source24 and or IMDs 14 to perform an action intended to equalize chargestates when multiple IMDs 14 receive power from charging device 20. Insome examples, this process may occur prior to the start of charging. Inother examples, charge states may be equalized during a charging sessionas each of IMDs 14 may receive different amounts of power if the primarycoil 48 shifts with respect to the different secondary coils of IMDs 14.Charging device 20 may periodically ping each IMD 14 for charge stateinformation and/or each IMD 14 may periodically report charge stateduring a charging session.

In other examples, IMDs 14 may communicate with each other and/orpartially or fully control charge state balancing between IMDs 14. Forexample, IMD1 may act as a master device that receives charge state datafrom a slave IMD2, determines which of IMD1 or IMD2 needs to perform apower consuming function to equalize charge state, and transmits acommand to IMD2 to perform a function as needed. As shown in the exampleof FIG. 5, multiple IMDs 14 receive energy via indicative coupling withcharging device 20 (110). For example, the primary coil 48 and thesecondary coils of the respective IMDs 14 may not necessarily be coupledin the same way. In some situations, charging device 20 may be closer toone of the two or more IMDs. In some situations, primary coil 48 may beoriented to better couple with the secondary coil of one IMD overanother. By using the systems and techniques described herein, two ormore IMDs may be recharged safely and efficiently regardless of thevariable distances between the IMDs and the charging device.

Processing circuitry 22 of IMD1 may determine the charge state of afirst rechargeable power source (e.g., the power source of IMD1) and thecharge state of a second rechargeable power source (e.g., the powersource of IMD2) (112). Processing circuitry 22 of IMD1 may then controlcharging of the first power source of IMD1 based on the charge state ofthe second power source of IMD2 (114). For example, during a rechargesession, if IMD1 is approaching a target charge state (e.g., fullcharge) before IMD2, then IMD1 may consume more power to reduce thecharge state and/or reduce the amount of recharge current that reachesits own power source, such as described herein. For example, IMD1 maydetune its charging circuitry 28 or open a circuit of its secondary coilto reduce the amount of current reaching the power source.Alternatively, IMD1 may directly send a command to IMD2 to reduce thecharge state of its power source and/or reduce the power that reachesthe power source of IMD2 if IMD2 has a higher charge state than IMD1.IMD1 and IMD2 may communicate directly or via charging device 20 and/orexternal programmer 19. IMD1 may continue to control IMD1 and/or IMD2 tomanage power consumption and/or received charging power based ondetermined charge state from each IMD (e.g., blocks 112 and 114) duringthe recharge session from charging device 20.

FIG. 6 is a flow diagram of an example technique for controllingcharging of a power source of a medical device (e.g., IMD 14) by anexternal charging device (e.g., charging device 20) based on temperatureof the IMD 14. Processing circuitry 50 of charging device 20 isdescribed in the example of FIG. 6. However, other devices andcircuitry, such as processing circuitry 22 of IMDs IMD 14A or 14B, orany combination thereof, may perform the features of FIG. 6.

In the example of FIG. 6, charging device 20 delivers recharge energy toIMDs 14 via indicative coupling (116). As described herein, multipleIMDs 14 may receive recharge energy, and each IMD may be monitored forcurrent charge state of the respective power source and temperate of therespective IMD. Processing circuitry 50 may control charging of powersource 24 of IMD1 (e.g., IMD 14A) based on the charge state of thecharge state of the power source of IMD2 (e.g., IMD 14B). For example,the power source of IMD2 may not charge as quickly due to inefficientinductive coupling or the charge state of IMD2 is initially lower thanthe charge state of IMD1.

During the charging session, processing circuitry 50 may determine if atemperature of IMD1 or IMD2 exceeds a maximum limit. IMD1 and IMD2 mayperiodically transmit the sensed temperature of the respective IMD. Ifprocessing circuitry 50 determines that the temperature of either IMD(or patient tissue in other examples) has not reached a maximumtemperature limit (“NO” branch of block 120), then processing circuitry50 continues to deliver energy for charging of both IMDs, such as untilboth IMDs have reached a target charge state (118). If the temperatureof either IMD1 or IMD2 has exceeded the maximum temperature limit (“YES”branch of block 120), then processing circuitry 50 controls the IMD thathas exceeded the temperature limit to reduce the temperature of the IMDto an acceptable level while charging device 20 continues to deliverenergy via inductive coupling (122). For example, processing circuitry50 may transmit a command to IMD1 via communication circuitry 56 (or viamodulated power delivery from primary coil 48) to perform one or morefunctions that may reduce the temperature of IMD1. The command mayinstruct IMD1 to detune circuitry of secondary coil 28 or even open acircuit of secondary coil 28 in order to reduce or eliminate electricalcurrent induced in secondary coil 28. In this manner, charging device 20may continue to charge IMD2 while also reducing the risk of IMD1overheating or delivering an undesired temperature to patient 12. Insome examples, processing circuitry 50 may control charging within IMD1and/or IMD2 based on thermal dosage to patient tissue and the state ofcharge of the power sources of each respective IMD1 and IMD2.

Although charging device 20 is described as performing the features ofFIG. 6, processing circuitry of one or more IMDs may perform thesefeatures in other examples. For example, processing circuitry of IMD1may self-monitor the temperature of IMD1 during a charging session andtake steps to reduce that temperature in response to detecting thetemperature exceeding the temperature limit. In this manner, IMD1 mayproactively reduce charging current induced from charging device 20 insituations where the inductive coupling is causing the temperature ofIMD1 to exceed the limit. The increase in temperature may be caused byresistive shunting of energy when the power source of IMD1 has reached afull charge state and/or if inductive coupling is generating too muchcurrent within IMD1. This could occur due to efficient coupling and/orthe patient is covering the IMD during charging such that the IMD is notcapable is dissipating heat through patient tissue.

The following numbered examples demonstrate one or more aspects of thisdisclosure.

Example 1

A medical device system includes: a first implantable medical device(IMD) including: stimulation circuitry configured to generatestimulation deliverable to a patient; a first rechargeable power source;and a secondary coil coupled to the first rechargeable power source, thesecondary coil configured to charge the first rechargeable power sourcevia inductive coupling with a primary coil of an external chargingdevice; and processing circuitry configured to control charging of thefirst rechargeable power source based on a charge state of a secondrechargeable power source of a second IMD.

Example 2

In some examples of the medical device system of example 1, theprocessing circuitry further configured to: identify a start to acharging session; determine that a charge state of the firstrechargeable power source is greater than a charge state of the secondrechargeable power source; and in response to the determination, controlincreasing consumption of charge stored by the first rechargeable powersource by the first IMD until the charge states of the first and secondrechargeable power sources are substantially equivalent.

Example 3

In some examples of the medical device system of examples 1 or 2, theprocessing circuitry is further configured to: determine that a chargestate of the first rechargeable power source is greater than a chargestate of the second rechargeable power source; and in response to thedetermination, control reducing a charging current to the firstrechargeable power source.

Example 4

In some examples of the medical device system of example 3, theprocessing circuitry controls reducing charging current to the firstrechargeable power source by at least one of: tuning a rectifier circuitof charging circuitry to a different frequency than a frequency ofrecharge energy delivered by the external charging device, controllingan oscillator to generate a different frequency than the frequency ofrecharge energy, or shunting the recharge energy through a resistiveload in the first IMD.

Example 5

In some examples of the medical device system of any of examples 1-4,the processing circuitry controls charging of the first rechargeablepower source by opening a circuit coupled to the secondary coil of thefirst IMD to prevent current from being induced in the secondary coil.

Example 6

In some examples of the medical device system of example 5, the medicaldevice system further includes timer circuitry configured to initiate acountdown when the processing circuitry open circuits the secondarycoil, and wherein, in response to the end of the countdown, theprocessing circuitry is configured to close the circuit coupled to thesecondary coil.

Example 7

In some examples of the medical device system of any of examples 1-6,the medical device system further includes a temperature sensor coupledto the processing circuitry, wherein the processing circuitry controlscharging of the first rechargeable power source based on a temperatureof the first IMD, and wherein, in response to the temperature sensorsensing that the temperature of the first IMD meets a maximumtemperature limit, the processing circuitry is configured to, at leastone of: control decreasing consumption of charge stored by the firstrechargeable power source by the first IMD, or close a circuit coupledto the secondary coil of the first IMD.

Example 8

In some examples of the medical device system of any of examples 1-7,the medical device system further includes communication circuitrycoupled to the processing circuitry, the communication circuitryconfigured to receive a first signal corresponding to a charge state ofthe first rechargeable power source and a second signal corresponding toa charge state of the second rechargeable power source, and wherein theprocessing circuitry is configured to control charging of the first andsecond rechargeable power sources based on the first and second signals.

Example 9

In an example, a method for controlling charging of a first rechargeablepower source of a first implantable medical device (IMD) in a patientincludes: receiving, at a secondary coil of the first IMD, energy viainductive coupling from a primary coil of an external charging device;controlling, by processing circuitry, charging of the first rechargeablepower source based on a charge state of a second rechargeable powersource of a second IMD.

Example 10

In some examples of the method of example 9, the method furtherincludes: identifying, by the processing circuitry, a charging session;determining, by the processing circuitry, that a charge state of thefirst rechargeable power source is greater than a charge state of thesecond rechargeable power source; and in response to the determination,controlling by the processing circuitry, increasing consumption ofcharge stored by the first rechargeable power source by the first IMDuntil the charge states of the first and second rechargeable powersources are substantially equivalent.

Example 11

In some examples of the method of example 9 or 10, the method furtherincludes: determining, by the processing circuitry, that a charge stateof the first rechargeable power source is greater than a charge state ofthe second rechargeable power source; and in response to thedetermination, controlling, by the processing circuitry, reducing acharging current to the first rechargeable power source.

Example 12

In some examples of the method of example 11, controlling reducing acharging current includes at least one of: tuning a rectifier circuit ofcharging circuitry to a different frequency than a frequency of rechargeenergy delivered by an external charging device, controlling anoscillator, or shunting the recharge energy through a resistive load inthe first IMD.

Example 13

In some examples of the method of any of examples 9-12, the methodfurther includes opening a circuit coupled to the secondary coil of thefirst IMD to prevent current from being induced in the secondary coil.

Example 14

In some examples of the method of example 13, the method furtherincludes initiating a countdown when the circuit the secondary coil isopen circuited, and closing the circuit coupled to the secondary coil inresponse to the end of the countdown.

Example 15

In some examples of the method of any of examples 9-14, the methodfurther includes: controlling charging of the first rechargeable powersource based on a temperature of the first IMD; and in response to thetemperature of the first IMD meeting a maximum temperature limit, atleast one of: controlling, by the processing circuitry, decreasingconsumption of charge stored by the first rechargeable power source bythe first IMD, or closing, by the processing circuitry, a circuitcoupled to the secondary coil of the first IMD.

Example 16

In some examples of the method of any of examples 9-15, the methodfurther includes receiving, at communication circuitry, a first signalcorresponding to a charge state of the first rechargeable power sourceand a second signal corresponding to a charge state of the secondrechargeable power source, and controlling, by the processing circuitry,charging of the first and second rechargeable power sources based on thefirst and second signals.

Example 17

In an example, a medical system includes: a first implantable medicaldevice (IMD) including: stimulation circuitry configured to generatestimulation deliverable to a patient; a first rechargeable power source;and a secondary coil coupled to the first rechargeable power source, thesecondary coil configured to charge the first rechargeable power sourcevia inductive coupling with a primary coil of an external chargingdevice; a second IMD including: stimulation circuitry configured togenerate stimulation deliverable to the patient; a second rechargeablepower source; and a secondary coil coupled to the second rechargeablepower source, the secondary coil configured to charge the secondrechargeable power source via inductive coupling with the primary coilof the external charging device; and processing circuitry configured to:determine a charge state of the first rechargeable power source and acharge state of the second rechargeable power source; control the firstIMD to achieve a target charge state of the first rechargeable powersource based on the charge state of the second rechargeable power sourceof the second IMD; and control delivering energy from the externalcharging device to the secondary coils coupled to the first and secondrechargeable power sources.

Example 18

In some examples of the medical system of example 17, the processingcircuitry is further configured to: identify a start of a chargingsession; determine that the charge state of the first rechargeable powersource is greater than the charge state of the second rechargeable powersource; and in response to the determination, control increasingconsumption of charge stored by the first rechargeable power source bythe first IMD until the charge states of the first and secondrechargeable power sources are substantially equivalent.

Example 19

In some examples of the medical system of example 17 or 18, theprocessing circuitry is further configured to: determine that the chargestate of the first rechargeable power source is greater than a chargestate of the second rechargeable power source; and in response to thedetermination, control reducing a charging current to the firstrechargeable power source by at least one of: tuning a rectifier circuitof charging circuitry to a different frequency than a frequency ofrecharge energy delivered by the external charging device, controllingan oscillator to generate a different frequency than the frequency ofrecharge energy, or shunting the recharge energy through a resistiveload.

Example 20

In some examples of the medical system of any of examples 17-19, theprocessing circuitry is further configured to: open a circuit coupled tothe secondary coil of the first IMD to prevent current from beinginduced in the secondary coil of the first IMD; and the medical systemfurther comprising timer circuitry configured to initiate a countdownwhen the processing circuitry open circuits the secondary coil of thefirst IMD, and wherein, in response to the end of the countdown, theprocessing circuitry is configured to close the circuit coupled to thesecondary coil.

Example 21

In an example, a method for controlling charging of a first rechargeablepower source of a first implantable medical device (IMD) in a patientincludes: determining, by processing circuitry, a charge state of thefirst rechargeable power source and a charge state of a secondrechargeable power source of a second IMD; controlling, by theprocessing circuitry, the first IMD to achieve a target charge state ofthe first rechargeable power source based on the charge state of thesecond rechargeable power source of the second IMD; and delivering, by aprimary coil and via inductive coupling, energy to the first and secondIMDs.

Example 22

In some examples of the method of example 21, the method furtherincludes: identifying, by the processing circuitry, a start of acharging session; determining, by the processing circuitry, that thecharge state of the first rechargeable power source is greater than thecharge state of the second rechargeable power source; and in response tothe determination, controlling, by the processing circuitry, increasingconsumption of charge stored by the first rechargeable power source bythe first IMD until the charge states of the first and secondrechargeable power sources are substantially equivalent.

Example 23

In some examples of the method of example 21 or 22, the method furtherincludes: determining, by the processing circuitry, that the chargestate of the first rechargeable power source is greater than a chargestate of the second rechargeable power source; and in response to thedetermination, controlling, by the processing circuitry, reducing acharging current to the first rechargeable power source by at least oneof: tuning a rectifier circuit of charging circuitry to a differentfrequency than a frequency of recharge energy delivered by an externalcharging device, controlling an oscillator to generate a differentfrequency than the frequency of recharge energy, or shunting therecharge energy through a resistive load.

Example 24

In some examples of the method of any of examples 21-23, the methodfurther includes: opening a circuit of a secondary coil of the first IMDto prevent current from being induced in the secondary coil; initiatinga countdown, by timer circuitry, when the circuit of the secondary coilis opened, and closing the circuit of the secondary coil in response tothe end of the countdown.

Example 25

In some examples, a system includes: means for determining, a chargestate of a first rechargeable power source of a first implantablemedical device (IMD) and a charge state of a second rechargeable powersource of a second IMD; means for controlling the first IMD to achieve atarget charge state of the first rechargeable power source based on thecharge state of the second rechargeable power source of the second IMD;and means for delivering energy to the first and second IMDs.

Example 26

In some examples, a non-transitory, computer-readable storage mediumincludes instructions that, when executed, cause one or more processorsto: determine a charge state of a first rechargeable power source of afirst implantable medical device (IMD) and a charge state of a secondrechargeable power source of a second IMD; control the first IMD toachieve a target charge state of the first rechargeable power sourcebased on the charge state of the second rechargeable power source of thesecond IMD; and deliver energy to the first and second IMDs.

The techniques described in this disclosure, including those attributedto system 10, IMDs 14, charging device 20, and programmer 19, andvarious constituent components, may be implemented, at least in part, inhardware, software, firmware or any combination thereof. For example,various aspects of the techniques may be implemented within one or moreprocessors or processing circuitry, including one or moremicroprocessors, DSPs, ASICs, FPGAs, or any other equivalent integratedor discrete logic circuitry, as well as any combinations of suchcomponents, remote servers, remote client devices, or other devices. Theterm “processor” or “processing circuitry” may generally refer to any ofthe foregoing logic circuitry, alone or in combination with other logiccircuitry, or any other equivalent circuitry.

Such hardware, software, firmware may be implemented within the samedevice or within separate devices to support the various operations andfunctions described in this disclosure. In addition, any of thedescribed units, modules or components may be implemented together orseparately as discrete but interoperable logic devices. Depiction ofdifferent features as modules or units is intended to highlightdifferent functional aspects and does not necessarily imply that suchmodules or units must be realized by separate hardware or softwarecomponents. Rather, functionality associated with one or more modules orunits may be performed by separate hardware or software components, orintegrated within common or separate hardware or software components.

The techniques or processes described in this disclosure may also beembodied or encoded in an article of manufacture including acomputer-readable storage medium encoded with instructions. Instructionsembedded or encoded in an article of manufacture including acomputer-readable storage medium encoded, may cause one or moreprogrammable processors, or other processors, to implement one or moreof the techniques described herein, such as when instructions includedor encoded in the computer-readable storage medium are executed by theone or more processors. Example computer-readable storage media mayinclude random access memory (RAM), read only memory (ROM), programmableread only memory (PROM), erasable programmable read only memory (EPROM),electronically erasable programmable read only memory (EEPROM),ferroelectric random access memory (FRAM), flash memory, a hard disk, acompact disc ROM (CD-ROM), a floppy disk, a cassette, magnetic media,optical media, or any other computer readable storage devices ortangible computer readable media. The computer-readable storage mediummay also be referred to as storage devices.

In some examples, a computer-readable storage medium comprisesnon-transitory medium. The term “non-transitory” may indicate that thestorage medium is not embodied in a carrier wave or a propagated signal.In certain examples, a non-transitory storage medium may store data thatcan, over time, change (e.g., in RAM or cache).

Various examples have been described herein. Any combination of thedescribed operations or functions is contemplated. These and otherexamples are within the scope of the following claims.

What is claimed is:
 1. A medical system comprising: a first implantablemedical device (IMD) comprising: circuitry configured to at least one ofdeliver a therapy to a patient or sense a physiological signal from thepatient; a first rechargeable power source; and a secondary coil coupledto the first rechargeable power source, the secondary coil configured tocharge the first rechargeable power source via inductive coupling with aprimary coil of an external charging device; and processing circuitryconfigured to control charging of the first rechargeable power sourcebased on a charge state of a second rechargeable power source of asecond IMD, wherein at least one of the first IMD, the second IMD, theexternal charging device, or an external programmer comprises theprocessing circuitry.
 2. The medical system of claim 1, wherein theprocessing circuitry is further configured to: identify a start to acharging session; determine that a charge state of the firstrechargeable power source is greater than a charge state of the secondrechargeable power source; and in response to the determination, controlincreasing consumption of charge stored by the first rechargeable powersource by the first IMD until the charge states of the first and secondrechargeable power sources are substantially equivalent.
 3. The medicalsystem of claim 1, wherein the processing circuitry is furtherconfigured to: determine that a charge state of the first rechargeablepower source is greater than a charge state of the second rechargeablepower source; and in response to the determination, control reducing acharging current to the first rechargeable power source.
 4. The medicalsystem of claim 3, wherein the processing circuitry controls reducingcharging current to the first rechargeable power source by at least oneof: tuning a rectifier circuit of charging circuitry to a differentfrequency than a frequency of recharge energy delivered by the externalcharging device, controlling an oscillator to generate a differentfrequency than the frequency of recharge energy, or shunting therecharge energy through a resistive load in the first IMD.
 5. Themedical system of claim 1, wherein the processing circuitry controlscharging of the first rechargeable power source by opening a circuitcoupled to the secondary coil of the first IMD to prevent current frombeing induced in the secondary coil.
 6. The medical system of claim 5,further comprising timer circuitry configured to initiate a countdownwhen the processing circuitry open circuits the secondary coil, andwherein, in response to the end of the countdown, the processingcircuitry is configured to close the circuit coupled to the secondarycoil.
 7. The medical system of claim 1, further comprising a temperaturesensor coupled to the processing circuitry, wherein the processingcircuitry controls charging of the first rechargeable power source basedon a temperature of the first IMD, and wherein, in response to thetemperature sensor sensing that the temperature of the first IMD meets amaximum temperature limit, the processing circuitry is configured to, atleast one of: control decreasing consumption of charge stored by thefirst rechargeable power source by the first IMD, or close a circuitcoupled to the secondary coil of the first IMD.
 8. The medical system ofclaim 1, further comprising communication circuitry coupled to theprocessing circuitry, the communication circuitry configured to receivea first signal corresponding to a charge state of the first rechargeablepower source and a second signal corresponding to a charge state of thesecond rechargeable power source, and wherein the processing circuitryis configured to control charging of the first and second rechargeablepower sources based on the first and second signals.
 9. The medicalsystem of claim 1, wherein the first IMD comprises the processingcircuitry.
 10. The medical system of claim 1, wherein the second IMDcomprises the processing circuitry.
 11. The medical system of claim 1,wherein the external charging device comprises the processing circuitry.12. The medical system of claim 1, wherein the external programmercomprises the processing circuitry.
 13. A method for controllingcharging of a first rechargeable power source of a first implantablemedical device (IMD) in a patient, the method comprising: receiving, ata secondary coil of the first IMD, energy via inductive coupling from aprimary coil of an external charging device; controlling, by processingcircuitry, charging of the first rechargeable power source based on acharge state of a second rechargeable power source of a second IMD,wherein at least one of the first IMD, the second IMD, the externalcharging device, or an external programmer comprises the processingcircuitry.
 14. The method of claim 13, further comprising: identifying,by the processing circuitry, a charging session; determining, by theprocessing circuitry, that a charge state of the first rechargeablepower source is greater than a charge state of the second rechargeablepower source; and in response to the determination, controlling by theprocessing circuitry, increasing consumption of charge stored by thefirst rechargeable power source by the first IMD until the charge statesof the first and second rechargeable power sources are substantiallyequivalent.
 15. The method of claim 13, further comprising: determining,by the processing circuitry, that a charge state of the firstrechargeable power source is greater than a charge state of the secondrechargeable power source; and in response to the determination,controlling, by the processing circuitry, reducing a charging current tothe first rechargeable power source.
 16. The method of claim 15, whereincontrolling reducing a charging current comprises at least one of:tuning a rectifier circuit of charging circuitry to a differentfrequency than a frequency of recharge energy delivered by an externalcharging device, controlling an oscillator, or shunting the rechargeenergy through a resistive load in the first IMD.
 17. The method ofclaim 13, further comprising opening a circuit coupled to the secondarycoil of the first IMD to prevent current from being induced in thesecondary coil.
 18. The method of claim 17, further comprisinginitiating a countdown when the circuit the secondary coil is opencircuited, and closing the circuit coupled to the secondary coil inresponse to the end of the countdown.
 19. The method of claim 13,further comprising: controlling charging of the first rechargeable powersource based on a temperature of the first 1 MB; and in response to thetemperature of the first 1 MB meeting a maximum temperature limit, atleast one of: controlling, by the processing circuitry, decreasingconsumption of charge stored by the first rechargeable power source bythe first 1 MB, or closing, by the processing circuitry, a circuitcoupled to the secondary coil of the first IMD.
 20. The method of claim13, further comprising receiving, at communication circuitry, a firstsignal corresponding to a charge state of the first rechargeable powersource and a second signal corresponding to a charge state of the secondrechargeable power source, and controlling, by the processing circuitry,charging of the first and second rechargeable power sources based on thefirst and second signals.
 21. A medical system comprising: a firstimplantable medical device (IMD) comprising: first circuitry configuredto at least one of deliver a first therapy to a patient or sense a firstphysiological signal from the patient; a first rechargeable powersource; and a secondary coil coupled to the first rechargeable powersource, the secondary coil configured to charge the first rechargeablepower source via inductive coupling with a primary coil of an externalcharging device; a second IMD comprising: second circuitry configured toat least one of deliver a second therapy to the patient or sense asecond physiological signal from the patient; a second rechargeablepower source; and a secondary coil coupled to the second rechargeablepower source, the secondary coil configured to charge the secondrechargeable power source via inductive coupling with the primary coilof the external charging device; and processing circuitry configured to:determine a charge state of the first rechargeable power source and acharge state of the second rechargeable power source; control the firstIMD to achieve a target charge state of the first rechargeable powersource based on the charge state of the second rechargeable power sourceof the second IMD; and control delivering energy from the externalcharging device to the secondary coils coupled to the first and secondrechargeable power sources, wherein at least one of the first IMD, thesecond IMD, the external charging device, or an external programmercomprises the processing circuitry.
 22. The medical system of claim 21,wherein the processing circuitry is further configured to: identify astart of a charging session; determine that the charge state of thefirst rechargeable power source is greater than the charge state of thesecond rechargeable power source; and in response to the determination,control increasing consumption of charge stored by the firstrechargeable power source by the first IMD until the charge states ofthe first and second rechargeable power sources are substantiallyequivalent.
 23. The medical system of claim 21, wherein the processingcircuitry is further configured to: determine that the charge state ofthe first rechargeable power source is greater than a charge state ofthe second rechargeable power source; and in response to thedetermination, control reducing a charging current to the firstrechargeable power source by at least one of: tuning a rectifier circuitof charging circuitry to a different frequency than a frequency ofrecharge energy delivered by the external charging device, controllingan oscillator to generate a different frequency than the frequency ofrecharge energy, or shunting the recharge energy through a resistiveload.
 24. The medical system of claim 21, wherein the processingcircuitry is further configured to: open a circuit coupled to thesecondary coil of the first IMD to prevent current from being induced inthe secondary coil of the first IMD; and the medical system furthercomprising timer circuitry configured to initiate a countdown when theprocessing circuitry open circuits the secondary coil of the first IMD,and wherein, in response to the end of the countdown, the processingcircuitry is configured to close the circuit coupled to the secondarycoil.
 25. A method for controlling charging of a first rechargeablepower source of a first implantable medical device (IMD) in a patient,the method comprising: determining, by processing circuitry, a chargestate of the first rechargeable power source and a charge state of asecond rechargeable power source of a second IMD; controlling, by theprocessing circuitry, the first IMD to achieve a target charge state ofthe first rechargeable power source based on the charge state of thesecond rechargeable power source of the second IMD; and delivering, by aprimary coil and via inductive coupling, energy to the first and secondIMDs.
 26. The method of claim 25, further comprising: identifying, bythe processing circuitry, a start of a charging session; determining, bythe processing circuitry, that the charge state of the firstrechargeable power source is greater than the charge state of the secondrechargeable power source; and in response to the determination,controlling, by the processing circuitry, increasing consumption ofcharge stored by the first rechargeable power source by the first IMDuntil the charge states of the first and second rechargeable powersources are substantially equivalent.
 27. The method of claim 25,further comprising: determining, by the processing circuitry, that thecharge state of the first rechargeable power source is greater than acharge state of the second rechargeable power source; and in response tothe determination, controlling, by the processing circuitry, reducing acharging current to the first rechargeable power source by at least oneof: tuning a rectifier circuit of charging circuitry to a differentfrequency than a frequency of recharge energy delivered by an externalcharging device, controlling an oscillator to generate a differentfrequency than the frequency of recharge energy, or shunting therecharge energy through a resistive load.
 28. The method of claim 25,further comprising: opening a circuit of a secondary coil of the firstIMD to prevent current from being induced in the secondary coil;initiating a countdown, by timer circuitry, when the circuit of thesecondary coil is opened, and closing the circuit of the secondary coilin response to the end of the countdown.